Recherche Images Maps Play YouTube Actualités Gmail Drive Plus »
Connexion
Les utilisateurs de lecteurs d'écran peuvent cliquer sur ce lien pour activer le mode d'accessibilité. Celui-ci propose les mêmes fonctionnalités principales, mais il est optimisé pour votre lecteur d'écran.

Brevets

  1. Recherche avancée dans les brevets
Numéro de publicationUS7776086 B2
Type de publicationOctroi
Numéro de demandeUS 10/837,402
Date de publication17 août 2010
Date de dépôt30 avr. 2004
Date de priorité30 avr. 2004
État de paiement des fraisPayé
Autre référence de publicationCA2563340A1, CA2563340C, EP1753371A2, US20050246015, WO2005107648A2, WO2005107648A3
Numéro de publication10837402, 837402, US 7776086 B2, US 7776086B2, US-B2-7776086, US7776086 B2, US7776086B2
InventeursTroy Miller
Cessionnaire d'origineRevision Optics, Inc.
Exporter la citationBiBTeX, EndNote, RefMan
Liens externes: USPTO, Cession USPTO, Espacenet
Aspherical corneal implant
US 7776086 B2
Résumé
A corneal implant having an aspheric surface for modifying the cornea curvature and altering the corneal refractive power. The corneal implant has a lens body formed of an optically clear bio-compatible material, preferably with an index of refraction substantially similar to that of human corneal tissue (1.376). The aspheric surface is comprised of a continuous aspheric surface from the apex of the implant to beveled surface. The beveled surface, positioned near the outer diameter of the implant, is used to reduce the thickness of the aspheric surface on the periphery of the lens to the outer diameter edge. The body of the implant has a diameter between about 2.0 mm and 7.0 mm and a thickness less than about 0.150 mm.
Images(5)
Previous page
Next page
Revendications(58)
1. A corneal implant, comprising:
a lens body formed of an optically clear, bio-compatible material, the lens body having an anterior surface and a posterior surface, and an outer diameter edge;
the bio-compatible material having a refractive index ranging from 1.36-1.39; and
the anterior surface being convex in shape and being formed with a continuous aspheric surface,
wherein the lens body is adapted to be disposed posterior to a first portion of the cornea and anterior to a second portion of the cornea when implanted,
wherein the continuous aspheric surface is defined by the formula:
X2+Y2+(1+Q)Z2+2ZR=0, wherein the Z axis is the optical axis of the implant, wherein the aspheric surface is a circularly symmetric surface about the Z axis with the apex of the surface at the coordinates X=0, Y=0, Z=0, wherein Z is the coordinate of the surface along the Z axis, wherein X and Y are the coordinates of the surface in the plane perpendicular to the Z axis, wherein R is the radius of curvature at the apex of the implant, and wherein Q is the surface asphericity of the aspheric surface and Q<0.
2. The implant of claim 1, wherein the posterior surface is concave in shape.
3. The implant of claim 2, wherein the posterior surface is curved in shape with a posterior radii of curvature.
4. The implant of claim 1, wherein the lens body has a thickness less than about 0.150 mm.
5. The implant of claim 1, wherein the lens body has a diameter between about 2.0 mm and about 7.0 mm.
6. The implant of claim 1, wherein the outer diameter edge has a thickness less than about 0.015 mm.
7. The implant of claim 1, wherein the outer diameter edge has a substantially planar surface.
8. The implant of claim 1, wherein the aspheric surface is adapted for the correction of presbyopia.
9. The implant of claim 1, wherein the aspheric surface is adapted for the correction of hyperopia.
10. The implant of claim 1, wherein the aspheric surface is adapted for the correction of myopia.
11. The implant of claim 1, wherein the lens body has a beveled surface connecting the outer diameter edge and the aspheric surface.
12. The implant of claim 11, wherein the beveled surface is substantially planar in a cross sectional side view of the lens body.
13. The implant of claim 11, wherein the anterior surface has an apex, and the continuous aspheric surface extends at least 1.0 mm radially outward from the apex.
14. The implant of claim 11, wherein the anterior surface has an apex, and the continuous aspheric surface extends from the apex to the beveled surface.
15. The implant of claim 1, wherein the lens body is circular in shape.
16. The implant of claim 1, wherein the optically clear, bio-compatible material is a permeable, microporous hydrogel.
17. The implant of claim 1, wherein then microporous hydrogel has a water content greater than 40% and up to approximately 90%.
18. A corneal implant, comprising:
a lens body formed of an optically clear, bio-compatible material, the lens body having an anterior surface with an apex and a posterior surface, and an outer diameter edge;
the bio-compatible material having a refractive index ranging from 1.36-1.39;
the anterior surface being convex in shape and being formed with a continuous aspheric surface,
wherein the lens body is adapted to be disposed posterior to a first portion of the cornea and anterior to a second portion of the cornea when implanted,
wherein every arc of the anterior surface extending from the apex to an outer edge of the anterior surface has a radius of curvature that varies along the entire length of the arc.
19. The implant of claim 18, wherein the lens body has a beveled surface connecting the outer diameter edge and the aspheric surface.
20. The implant of claim 18, wherein the posterior surface is concave in shape.
21. The implant of claim 20, wherein the posterior surface is curved in shape with a posterior radii of curvature.
22. The implant of claim 18, wherein the aspheric surface is adapted for the correction of presbyopia.
23. The implant of claim 18, wherein the aspheric surface is adapted for the correction of hyperopia.
24. The implant of claim 18, wherein the aspheric surface is adapted for the correction of myopia.
25. The implant of claim 19, wherein the beveled surface is substantially planar in a cross sectional side view of the lens body.
26. The implant of claim 19, wherein the continuous aspheric surface extends from the apex to the beveled surface.
27. The implant of claim 18, wherein the lens body is circular in shape.
28. The implant of claim 18, wherein the continuous aspheric surface extends at least 1.0 mm radially outward from the apex.
29. The implant of claim 18, wherein the optically, clear bio-compatible material is a permeable, microporous hydrogel.
30. The implant of claim 29, wherein then microporous hydrogel has a water content greater than 40% and up to approximately 90%.
31. The implant of claim 18, wherein the aspheric surface is defined by the formula: X2+Y2+(1+Q)Z2−2ZR=0, wherein the Z axis is the optical axis of the implant, wherein the aspheric surface is a circularly symmetric surface about the Z axis with the apex of the surface at the coordinates X=0, Y=0, Z=0, wherein Z is the coordinate of the surface along the Z axis, wherein X and Y are the coordinates of the surface in the plane perpendicular to the Z axis, wherein R is the radius of curvature at the apex of the implant, and wherein Q is the surface asphericity of the aspheric surface and Q<0.
32. A corneal implant, comprising:
a lens body formed of an optically clear microporous hydrogel, the lens body having an anterior surface and a posterior surface, and an outer diameter edge, the outer diameter edge having a thickness less than about 0.015 mm, the lens body having a diameter between about 2.0 mm and 7.0 mm;
the bio-compatible material having a refractive index ranging from 1.36-1.39; and the anterior surface being convex in shape and being formed with a continuous aspheric surface,
wherein the lens body has a beveled surface connecting the outer diameter edge and the aspheric surface,
wherein the lens body is adapted to be disposed posterior to a first portion of the cornea and anterior to a second portion of the cornea when implanted,
wherein the aspheric surface is defined by the formula:
X2+Y2+(1+Q)Z2−2ZR=0, wherein the Z axis is the optical axis of the implant, wherein the aspheric surface is a circularly symmetric surface about the Z axis with the apex of the surface at the coordinates X=0, Y=0, Z=0, wherein Z is the coordinate of the surface along the Z axis, wherein X and Y are the coordinates of the surface in the plane perpendicular to the Z axis, wherein R is the radius of curvature at the apex of the implant, and wherein Q is the surface asphericity of the aspheric surface and Q<0.
33. The implant of claim 32, wherein the lens body is circular in shape.
34. The implant of claim 32, wherein the outer diameter edge has a substantially planar surface.
35. The implant of claim 32, wherein the aspheric surface is adapted for the correction of presbyopia.
36. The implant of claim 32, wherein the aspheric surface is adapted for the correction of hyperopia.
37. The implant of claim 32, wherein the aspheric surface is adapted for the correction of myopia.
38. The implant of claim 32, wherein the anterior surface has an apex, and the continuous aspheric surface extends from the apex to the beveled surface.
39. The implant of claim 32, wherein the lens body is circular in shape.
40. The implant of claim 32, wherein the anterior surface has an apex, and the continuous aspheric surface extends at least 1.0 mm radially outward from the apex.
41. The implant of claim 32, wherein then microporous hydrogel has a water content greater than 40% and up to approximately 90%.
42. A method of implanting a corneal implant, said method comprising the steps of:
(a) cutting away a portion of the outer surface of a cornea;
(b) implanting a lens on the exposed surface of the cornea, said lens having a lens body formed of an optically clear, bio-compatible material, the lens body having an anterior surface with an apex and a posterior surface, and an outer diameter edge, the bio-compatible material having a refractive index ranging from 1.36-1.39, and the anterior surface being convex in shape and being formed with a continuous aspheric surface,
wherein every arc of the anterior surface extending from the apex to an outer edge of the anterior surface has a radius of curvature that varies along the entire length of the arc; and
(c) replacing the portion of the cornea that was cut away.
43. The method of claim 42, wherein the posterior surface is concave in shape.
44. The method of claim 43, wherein the posterior surface is curved in shape with a posterior radii of curvature.
45. The method of claim 42, wherein the lens body has a thickness less than about 0.150 mm.
46. The method of claim 42, wherein the lens body has a diameter between about 2.0 mm and about 7.0 mm.
47. The method of claim 42, wherein the outer diameter edge has a thickness less than about 0.015 mm.
48. The method of claim 42, wherein the outer diameter edge has a substantially planar surface in a cross sectional side view of the lens body.
49. The method of claim 42, wherein the aspheric surface is adapted for the correction of presbyopia.
50. The method of claim 42, wherein the aspheric surface is adapted for the correction of hyperopia.
51. The method of claim 42, wherein the aspheric surface is adapted for the correction of myopia.
52. The method of claim 42, wherein the lens body has a beveled surface connecting the outer diameter edge and the aspheric surface.
53. The method of claim 52, wherein the anterior surface has an apex, and the continuous aspheric surface extends at least 1.0 mm radially outward from the apex.
54. The method of claim 52, wherein the anterior surface has an apex, and the continuous aspheric surface extends from the apex to the beveled surface.
55. The method of claim 42, wherein the lens body is circular in shape.
56. The method of claim 42, wherein the optically clear, bio-compatible material is a permeable, microporous hydrogel.
57. The method of claim 42, wherein then microporous hydrogel has a water content greater than 40% and up to approximately 90%.
58. The method of claim 42, wherein the aspheric surface is defined by the formula: X2+Y2+(1+Q)Z2−2ZR=0, wherein the Z axis is the optical axis of the implant, wherein the aspheric surface is a circularly symmetric surface about the Z axis with the apex of the surface at the coordinates X=0, Y=0, Z=0, wherein Z is the coordinate of the surface along the Z axis, wherein X and Y are the coordinates of the surface in the plane perpendicular to the Z axis, wherein R is the radius of curvature at the apex of the implant, and wherein Q is the surface asphericity of the aspheric surface and Q<0.
Description
TECHNICAL FIELD

The field of this invention relates to prosthetic implants designed to be implanted in the cornea. More particularly, the invention relates to a corneal implant having an aspheric surface for modifying the cornea curvature and altering the corneal refractive power.

BACKGROUND OF THE INVENTION

Normal vision occurs when light that passes through and is refracted by the cornea, the lens, and other portions of the eye, and converges at or near the retina. Myopia or near-sightedness occurs when the light converges at a point before it reaches the retina and, conversely, hyperopia or far-sightedness occurs when the light converges a point beyond the retina. Other abnormal conditions include astigmatism where the outer surface of the cornea is irregular in shape and effects the ability of light to be refracted by the cornea. In addition, in patients who are older, a condition called presbyopia occurs in which there is a diminished power of accommodation of the natural lens resulting from the loss of elasticity of the lens, typically becoming significant after the age of 45.

Corrections for these conditions through the use of implants within the human cornea have been suggested. Various designs for such implants include solid, ring shaped, and split-ring shaped, circular flexible body members and other types of ring-shaped devices that are adjustable. These implants are inserted within the body of the cornea for changing the shape of the cornea, thereby altering its refractive power.

Generally, the human cornea flattens away from the center. The reasons are not completely clear, though one known factor is that as the cornea flattens it reduces the spherical aberration. Therefore, I consider it desirable to reshape the cornea and maintain an aspheric surface that naturally occurs while correcting for refractive error. I believe there is a demonstrated need for a more effective corneal implant that has an aspheric surface that will correspond more naturally to the surface of the human eye to address the problems as previously discussed.

BRIEF SUMMARY OF THE INVENTION

The present invention is directed to prosthetic implants designed to be implanted in the cornea. More particularly, the invention relates to a corneal implant having an aspheric surface for modifying the cornea curvature and altering the corneal refractive power. The implant has a continuous aspheric surface extending from a center point or apex of the anterior surface of the lens body. This continuous aspheric surface preferably extends for a radius of at least 1 mm from the center or apex of the lens body. The continuous aspheric surface is continually aspheric along the surface and does not contain any portion of the aspherical surface that is spherical.

The lens body is preferably formed of an optically clear bio-compatible material. The bio-compatible material has an index of refraction substantially similar to that of human corneal tissue (1.376). Thus, in a preferred embodiment, the refractive index of the implant material should be in the range of 1.36-1.39. Having such a refractive index prevents optical aberrations due to edge effects at the cornea-implant interface.

The optically clear bio-compatible material is preferably made from a visually clear, permeable, microporous hydrogel with a water content greater than 40% up to approximately 90%. Other suitable bio-compatible materials, however, may be used.

The lens body has an anterior surface, a posterior surface, and an outer diameter edge. The anterior surface is generally convex in shape with a continuous aspheric surface. In one embodiment, the posterior surface is concave in shape with a posterior radii of curvature. However, the posterior surface may shaped differently, such as being substantially planar, having multiple radii of curvature, and other shapes as would be readily useful.

In a preferred embodiment, the lens body has a thickness less than about 0.150 mm, an outer diameter edge thickness of about 0.015 mm, and a diameter between about 2.0 mm and about 7.0 mm.

The implant may be formed with a beveled surface. The beveled surface assists in maintaining the required edge thickness while increasing lens strength. Preferably, the beveled surface has a convex shape that has a partially spherical or partially aspherical surface.

In one aspect of the invention, there is a method of implanting the various embodiments of the inventive corneal implant as described herein. The method includes the steps of (a) cutting away a portion of the outer surface of a cornea; (b) implanting a lens on the exposed surface of the cornea, the lens having a lens body formed of an optically clear, bio-compatible material, the lens body having an anterior surface and a posterior surface, and an outer diameter edge; the bio-compatible material having a refractive index ranging from 1.36-1.39, and the anterior surface being convex in shape with a continuous aspheric surface; and (c) replacing the portion of the cornea that was cut away.

The foregoing has outlined rather broadly the features and technical advantages of the present invention in order that the detailed description of the invention that follows may be better understood. Additional features and advantages of the invention will be described hereinafter which form the subject of the claims of the invention. It should be appreciated that the conception and specific embodiment disclosed may be readily utilized as a basis for modifying or designing other structures for carrying out the same purposes of the present invention. It should also be realized that such equivalent constructions do not depart from the invention as set forth in the appended claims. The novel features which are believed to be characteristic of the invention, both as to its organization and method of operation, together with further objects and advantages will be better understood from the following description when considered in connection with the accompanying figures. It is to be expressly understood, however, that each of the figures is provided for the purpose of illustration and description only and is not intended as a definition of the limits of the present invention.

BRIEF DESCRIPTION OF THE DRAWINGS

For a more complete understanding of the present invention, reference is now made to the following descriptions taken in conjunction with the accompanying drawing, in which:

FIG. 1A is a top of an embodiment of the corneal implant;

FIG. 1B is a 3-dimensional, cross-sectional view A-A of the implant of FIG. 1A;

FIG. 1C is a 3-dimensional, cross-sectional view of the area B of FIG. 1B;

FIG. 2 is a cross-sectional view illustrating the nature of an aspherical continues surface;

FIG. 3 is a diagram showing the effect of asphericity on the shape of a concoid;

FIGS. 4A and 4B are schematic representations of a lamellar dissectomy, with FIG. 4B showing in particular the portion of the dissected cornea being connected through a hinge to the intact cornea; and

FIG. 4C is a schematic representations of a cornea in which the corneal implant have been implanted.

DETAILED DESCRIPTION OF THE INVENTION

As used herein, the term “a” or “an” may mean one or more. As used herein in the claim(s), when used in conjunction with the word “comprising”, the words “a” or “an” may mean one or more than one. As used herein, “another” may mean at least a second or more.

As used herein, the term “mm” means the unit of measurement in millimeters.

Most current surgical procedures are just coming of age in regards to aspheric surfacing. There is considerable published data on the anterior corneal surface asphericity. The common corneal shape is either a conic in certain sections or conicoids using three-dimensional data. The results are usually expressed in terms of asphericity Q, shape factor p or the eccentricity e. The mean values of the corneal surface are in the approximate range Q=−0.2 to −0.3. One thought is that the reason the human cornea flattens is to reduce spherical aberration.

When spherical aberration is present, non-paraxial rays do not intersect at the paraxial focus. By producing a spherical surface on the eye, the amount of asphericity is reduced that the cornea has and in turn, a spherical aberration is created. In most accounts the result will be a better near visual acuity because the center rays are still basically unaffected, but the intermediate and distance can loose some visual acuity.

To decrease the spherical aberration and also correct for visual disorders, one must look at the following. Maintain the natural aspheric surface that the cornea has, and flatten or steepen the cornea at the same time.

By doing the described, the central rays can be left as they are or increased (in the case of presbyopia) and at the same time flatten or decrease the radius from apex to the edge, bringing all rays within the paraxial focus. The actual radius is determined by what correction is needed to correct the visual disorder. All radius of curvature are dependent on the individual refraction of a patient.

Referring to FIG. 1A-1B, an embodiment of the aspherical corneal implant is shown. FIG. 1A is a top view of the implant. The implant 10 has a diameter (as shown by arrows 11-11) in the range of about 2.00 mm to 7.00 mm. The anterior surface 14 of the implant 10 has an aspheric surface 12 that is generally convex in shape. The aspheric surface 12 is comprised of a continuous aspheric surface from apex 18 to the transition zone 22. The transition zone 22 is the junction that begins the beveled surface 20. The beveled surface 20 is used to reduce the thickness of the aspheric surface 12 on the periphery of the lens to the outer diameter edge 24. Given that the implant 10 has a maximum useful diameter for implantation into the human cornea the implant without the beveled surface, would be too thick at the edges to properly seat the implant into the cornea. An edge thickness as specified prevents stacking and recruitment of keratocytes in the lens material so that keratocyte stacking and recruitment does not take place. This in turn eliminates unorganized collagen that forms undesirable scar tissue and infiltrates the lens, which tends to compromise the efficacy of the lens.

Referring now to FIG. 1B, a 3-dimensional, cross-sectional view of the implant 10 of FIG. 1A is shown. The implant 10 has an aspheric surface 12 from the apex 18 of the anterior surface of the lens to a transition zone 22. The radius of the aspheric surface 12 extends from the apex 18 outward towards the outer diameter edge 24. This radius is not less than 1.0 mm and the radius is not greater than the total radius to the beginning of the transition zone 22.

The implant 10 has a posterior surface 16 that is generally concave in shape. Where the implant is circular in shape, the apex 18 is also the center point of the lens. In one embodiment, the lens body has a thickness (as indicated by arrows 19-19) of less than about 0.150 mm. The center of the lens in most cases is the thickest part of the lens.

In a preferred embodiment, the posterior surface 16 is concave in shape with a posterior radii of curvature. However, the posterior surface 16 may shaped differently, such as being substantially flat or planar, having multiple radii of curvature, or utilizing other shapes as would be readily useful. In these other embodiments where a different shape posterior surface is utilized, than the thickness of the implant at its center may be greater than 0.150 mm. However, when using a concave shaped poster surface 16, preferably the thickness should be less than about 0.150 mm.

FIG. 1C is a close-up view of the area designated by the letter B in FIG. 1B. Preferably, the implant 10 has an outer diameter edge 24 that has substantially planar surface. The outer diameter edge 24 surface may also be spherical, or of other shapes that would be useful. Preferably, the outer diameter edge 24 has a thickness of about 0.015 mm. The thickness of the outer diameter edge is illustrated by arrows 25-25.

A beveled surface 20 transitions the anterior portion of the outer diameter edge 24 with the aspheric surface 12. In one embodiment, the shape of the surface of the beveled surface is substantially spherical with a radii of curvature, but in other embodiments may be substantially aspherical, substantially planar or other of useful shapes. Preferably, where the beveled surface 20 is spherical, the beveled has a single radii of curvature. The beveled surface 20 has a radius between about radius 1.5 mm-10.5 mm depending on the width of the implant. The beveled surface 20 and the aspheric surface 12 intersect at a junction 22. This junction 22 is referred herein, interchangeably, as the transition zone 22. The transition zone 22 provides a smooth transition from the beveled surface 20 to the aspheric surface 12. The transition zone 22 is preferably aspheric.

In one embodiment, the aspheric surface 12 comprises a continuous aspheric surface with a Q-value of less than zero, wherein Q is the surface asphericity and Q<0 represents a surface that flattens away from its vertex. The aspheric surface 12 may have a single Q-value or multiple Q-values for different zones on the surface of the implant, with each Q-value being less than zero. This can be expressed in terms of quantity p called the shape factor, which is related to Q by the equation p=1+Q or as eccentricity which is related to Q by the equation Q=−e2.

Q is represented by the following equation—
h 2+(1+Q)Z 2−2ZR=0

    • where the Z axis is the optical axis,
    • where h2=X2+Y2, and
    • where X, Y are distances perpendicular to optical axis,
    • where R is the vertex or apex radius of curvature.

Q is the surface asphericity, where

    • Q<−1 specifies a hyperboloid,
    • Q=−1 specifies a paraboloid,
    • −1<Q<0 specifies an ellipsoid, with the Z-axis being the major axis,
    • Q=0 specifies a sphere,
    • Q>0 specifies an ellipsoid with the major axis in the X-Y plane.

Referring to FIG. 3, the effect of asphericity on the shape of a concoid is shown. All of the curves have the same apex radius of curvature. The figure shows an -X, -Y, -Z axis with the particular axis labeled respectively. The general Q value equation discussed above is diagramatically illustrated in the figure: Ellipsoids, Sphere, Hyperboloids, and Paraboloids.

By varying the Q value of the aspheric surface 12, the corneal implant 10 aids in the correction of presbyopia, hyperopia, myopia or the combination thereof, while maintaining an the actual corneal surface of the eye in an aspheric manner. The following Table 1 illustrates different Q values for different lens parameters. Table 1 is merely illustrative and should not be construed to limit the size and ranges of the various parameters shown.

TABLE 1
Anterior Anterior Anterior Anterior
Approximant Posterior Apex End Semi- Asphericity
Diopter Change Radius Radius Radius Diameter (Q)
1.25 7.500 7.147 7.508 3.820 −0.118
1.75 7.500 7.081 7.508 3.820 −0.138
2.25 7.500 7.014 7.508 3.820 −0.158
2.75 7.500 6.949 7.508 3.820 −0.176
3.25 7.500 6.884 7.508 3.820 −0.195
3.75 7.500 6.822 7.508 3.820 −0.212
4.25 7.500 6.760 7.508 3.820 −0.228
4.75 7.500 6.700 7.508 3.820 −0.244

As used in Table 1, the column labeled Approximant Diopter Change refers to the projected diopter power change from the apex (center) of the lens to transition zone of the lens when implanted into the cornea. Whereas the center value would be +4.00 diopters the edge would have a value of 2.25 diopters less positive power. The lens anterior surface progressively changes from apex to edge. The table above is only a representative sample of diopter changes. For example, the diopter change for the corneal implant 10 may range from 0.12 diopter to 10 diopters for a given implant. The particular diopter for a corneal implant 10 will depend on a given patient'corrective needs.

The column labeled Posterior Radius refers to the back surface of the lens having contact with the stromal bed. The value for the Posterior Radius as used in Table 1 is measured in millimeters. Table 1 illustrates utilizing a posterior radius of 7.5 mm for each of the listed implants. The posterior radius may be varied depending on the particular posterior radius desired. In other embodiments, the posterior surface does not have a posterior radius of curvature, but is instead flat or has some other shaped surface or is textured.

The column labeled Anterior Apex Radius refers to the radius at the optical axis, or apex (center) in millimeters, needed to achieve desired corneal shape.

The column labeled Anterior End Radius refers to the target radius in millimeters at the end of the aspheric zone or outside diameter of said zone needed to achieve desired corneal shape.

The column labeled Anterior Semi-Diameter refers to the diameter of the desired aspheric zone measured in millimeters.

The column labeled Anterior Asphericity is the resultant Q value. In the examples shown in Table 1, the resultant Q value indicates that the anterior aspheric surface of the lens has a an aspheric ellipsoidal shape.

Referring now to FIG. 2, an example of an aspheric surface is shown. Line 23 is perpendicular to line 25. Point 26 is on line 23 which passes through the apex of the implant 10. FIG. 2 is not drawn completely to scale, but nevertheless illustrates the nature of the aspheric surface. The radius from point 26 to the surface indicated by arrow 30 is a radius of 6.6961 mm. The radius from point 26 to the surface indicated by arrow 31 is a radius of 6.7196. The follow Table 2 shows the remaining indicated radii from point 26.

TABLE 2
Arrow Radii in mm
32 6.7432
33 6.7683
34 6.7918
35 6.8154
36 6.8389
37 6.8640
38 6.8876
39 6.9111
40 6.9410

The particular points of the aspheric surface 12 show in FIG. 2 that the radii of curvature from point 26 increases from the apex 18 as the surface moves towards the outer edge of the implant. In a normal spherical surface, a lens would have a constant radii of curvature along the surface of the lens. As shown in FIG. 2, the inventive corneal implant 10 does not have a spherical surface, but instead a continuous aspheric surface from the apex of the implant.

The corneal implant 10 with the aspheric when implant is designed to reshape or re-contour the surface of the cornea by steepening or flattening the overall radius of curvature of the human cornea, while maintaining the correct natural aspheric surface.

In various embodiment, the corneal implant 10 with the aspheric surface can simultaneously correct the refractive error for distance vision (farsighted) and correct for near vision (reading). To achieve this, additional power is added to the central portion of the lens to correct the (reading add). For example, a patient with a refractive error of +3.00 diopters for distance, a positive 2 diopters is added to this needed distance correction for reading. This calculates to a starting diopter power at the apex of the corneal implant of +5.00 diopters which will progressively change to +3.00 diopters at the outer edge.

Taking the +5.00 diopters at apex the Q value can be calculated that is required to bring the lens surface (or cornea) from +5.00 diopters to +3.00 diopters within a designed lens diameter. An example would be to set the apex start at +5.00 and reduce the amount of aspheric change to within only 2.00 mm of the central portion of the lens. This result would then set this area of the lens to change progressively from +5.00 diopter to +4.50 diopters. From this point of 2.00 mm to 5.00 mm (remainder of lens) the asphericity can be set at a value to bring the remainder of the lens progressively from the +4.50 diopter to the required +3.00 diopter that the patient needed for distance correction. With this aspheric re-contouring using the inventive corneal implant 10, progressive change can be made which follow the natural shape of the human cornea.

The corneal implant 10 has a lens body formed of an optically clear bio-compatible material. In a preferred embodiment, the bio-compatible material has an index of refraction substantially similar to that of human corneal tissue (1.376). Thus, in a preferred embodiment, the refractive index of the implant material should be in the range of 1.36-1.39. Having such a refractive index prevents optical aberrations due to edge effects at the cornea-implant interface.

The corneal implant 10 is preferably made from a visually clear, permeable, microporous hydrogel with a water content greater than 40% up to approximately 90%. In other embodiments, the refractive index may be different from the refractive index of the corneal tissue. In such embodiments, in addition to the change in the shape of the cornea caused by the implantation of the lens, the actual material would have a refractive effect. Other embodiments from which the corneal implant may be made, include: polymethlmethacrylate (PMMA), silicone polymers, UV-absorbing acrylic, hydrogel, microporous hydrogel, collamer, collagel acrylic polymers, and other composite materials.

The present corneal implant 10 can be implanted in the cornea using a lamellar dissectomy shown schematically in FIGS. 4A, 4B. In this procedure, a keratome (not shown) is used in a known way to cut a portion of the outer surface of the cornea along line 42 as shown in FIG. 4A. This type of cut is used to form a corneal flap 44 shown in FIG. 4B, which remains attached to the cornea 40 through what is called a hinge 46. The hinge 46 is useful for allowing the flap 44 to be replaced with the same orientation as before the cut.

As is also known in the art, the flap is cut deeply enough to dissect the Bowman's membrane portion of the cornea, such as in keratome surgery or for subsequent moving of the tissue by laser or surgical removal. Other known techniques of cutting a flap in the cornea, such a utilizing a laser to create a flap or a pocket in which to place the implant, may also be used. A corneal flap of 100 to 200 microns, typically 160 to 200 microns, is made to eliminate the Bowman's membrane tension (which minimizes corneal nerve damage). This helps to conform the flap to the lens surface, thereby transferring all of the change of the shape to the anterior surface of the cornea. This makes refractive correction more reliable and predictable. Also, the possibility of extrusion of the implants is reduced due to pressure generated within the cornea caused by the addition of the implant. The corneal implant 10 is shown implanted in the cornea in FIG. 4C respectively, after the flap has been replaced in its normal position. These figures show the corrected shape for the outer surface of the cornea as a result of implants of the shapes described.

Although the present invention and its advantages have been described in detail, it should be understood that various changes, substitutions and alterations can be made herein without departing from the invention as defined by the appended claims. Moreover, the scope of the present application is not intended to be limited to the particular embodiments of the process, machine, manufacture, composition of matter, means, methods and steps described in the specification. As one will readily appreciate from the disclosure, processes, machines, manufacture, compositions of matter, means, methods, or steps, presently existing or later to be developed that perform substantially the same function or achieve substantially the same result as the corresponding embodiments described herein may be utilized. Accordingly, the appended claims are intended to include within their scope such processes, machines, manufacture, compositions of matter, means, methods, or steps.

Citations de brevets
Brevet cité Date de dépôt Date de publication Déposant Titre
US31681007 déc. 19622 févr. 1965Alvido R RichContact lens dipper assembly
US33436572 sept. 196626 sept. 1967Reuben F SpeshyockContact lens conditioning facility
US337920024 oct. 196523 avr. 1968Ruth M. PennellLens containtr
US34829064 oct. 19659 déc. 1969David VolkAspheric corneal contact lens series
US374333726 juil. 19713 juil. 1973E CraryContact lens inserter
US37701133 mars 19726 nov. 1973Mcd CorpContact lens holder
US387907627 déc. 197322 avr. 1975Robert O BarnettMethod and apparatus for applying and removing a soft contact lens
US395031528 juin 197313 avr. 1976E. I. Du Pont De Nemours And CompanyContact lens having an optimum combination of properties
US403048013 mai 197621 juin 1977Ernst Jochen MeyerOcular decompression process
US40376045 janv. 197626 juil. 1977Newkirk John BArtifical biological drainage device
US403982726 août 19762 août 1977American Optical CorporationMethod for marking intraocular lenses
US407127227 sept. 197631 janv. 1978Drdlik Frank JContact lens applicator
US415771831 août 197712 juin 1979The United States Of America As Represented By The Administrator Of The National Aeronautics And Space AdministrationIntra-ocular pressure normalization technique and equipment
US418449131 août 197722 janv. 1980The United States Of America As Represented By The Administrator Of The National Aeronautics And Space AdministrationIntra-ocular pressure normalization technique and equipment
US419481410 nov. 197725 mars 1980Bausch & Lomb IncorporatedTransparent opthalmic lens having engraved surface indicia
US42385246 mars 19789 déc. 1980American Optical CorporationProcess for identification marking clear plastic articles
US425752116 nov. 197924 mars 1981Stanley PolerPackaging means for an intraocular lens
US426813311 oct. 197919 mai 1981Bausch & Lomb IncorporatedPreferential orientation of contact lenses
US432630616 déc. 198027 avr. 1982Lynell Medical Technology, Inc.Intraocular lens and manipulating tool therefor
US439256915 janv. 198212 juil. 1983Shoup Leo ESoft contact lens asepticizing case
US44189919 juin 19806 déc. 1983Breger Joseph LPresbyopic contact lens
US442380922 juil. 19823 janv. 1984Staar Surgical Company, Inc.Packaging system for intraocular lens structures
US442874629 juil. 198131 janv. 1984Antonio MendezGlaucoma treatment device
US44522354 janv. 19825 juin 1984Reynolds Alvin EMethod for corneal curvature adjustment
US446670530 sept. 198221 août 1984Michelson Paul EFluid lens
US449086021 mars 19831 janv. 1985Ioptex Inc.Intraocular lens apparatus and method for implantation of same
US4504982 *5 août 198219 mars 1985Optical Radiation CorporationAspheric intraocular lens
US452121027 déc. 19824 juin 1985Wong Vernon GEye implant for relieving glaucoma, and device and method for use therewith
US45250445 mai 198325 juin 1985Bauman Robert CSoft contact lens with surface identification and method of using same
US454547829 févr. 19848 oct. 1985Fred WaldmanHard contact lens suction cups and method for their production
US45541155 juil. 198419 nov. 1985Neefe Charles WMethod of controlling the convex curve of soft lenses
US455491828 juil. 198226 nov. 1985White Thomas COcular pressure relief device
US4565198 *27 déc. 198321 janv. 1986Barnes-Hind, Inc.Method for altering the curvature of the cornea
US4580882 *21 avr. 19838 avr. 1986Benjamin NuchmanContinuously variable contact lens
US45869296 avr. 19846 mai 1986Binder Perry SHydrogel keratoprosthesis
US460408721 juin 19855 août 1986Joseph Neil HAqueous humor drainage device
US461691024 févr. 198414 oct. 1986Klein Robert EVisual indicator on soft contact lenses
US46182277 oct. 198321 oct. 1986Vistakon, Inc.Soft contact lens
US46192568 sept. 198228 oct. 1986Gerald HornIntraocular lens inserting assembly
US462466926 sept. 198425 nov. 1986Surgidev CorporationCorneal inlay with holes
US46405952 mai 19843 févr. 1987David VolkAspheric contact lens
US464672012 mars 19853 mars 1987Peyman Gholam AOptical assembly permanently attached to the cornea
US465577419 mars 19867 avr. 1987Choyce D PeterIntra-corneal implant for correction of aniridia
US466237014 nov. 19845 mai 1987Carl-Zeiss-StiftungApparatus for performing lamellar refractive corneal surgery
US466335825 avr. 19865 mai 1987Biomaterials Universe, Inc.Porous and transparent poly(vinyl alcohol) gel and method of manufacturing the same
US467127613 févr. 19849 juin 1987Kera AssociatesApparatus for corneal curvature adjustment
US467679210 nov. 198630 juin 1987Donald PraegerMethod and artificial intraocular lens device for the phakic treatment of myopia
US469769718 août 19866 oct. 1987Coopervision, Inc.Method and apparatus for packaging an intraocular lens
US470224427 févr. 198627 oct. 1987Staar Surgical CompanySurgical device for implantation of a deformable intraocular lens
US47509015 mars 198714 juin 1988Molteno Anthony C BImplant for drainage of aqueous humour
US476249613 févr. 19879 août 1988William F. MaloneyOphthalmologic lens phantom system
US47668953 févr. 198730 août 1988Kera Corneal Devices, Inc.Apparatus for corneal curvature adjustment
US480638210 avr. 198721 févr. 1989University Of FloridaOcular implants and methods for their manufacture
US483620124 mars 19886 juin 1989Patton Medical Technologies, Inc."Envelope" apparatus for inserting intra-ocular lens into the eye
US484017522 janv. 198820 juin 1989Peyman Gholam AMethod for modifying corneal curvature
US4842599 *12 nov. 198727 juin 1989Ann M. BronsteinProsthetic cornea and method of implantation therefor
US48442422 sept. 19874 juil. 1989The Johns Hopkins UniversityCornea retainer
US48510035 janv. 198825 juil. 1989Lindstrom Richard LCorneal implant lens with fixation holes
US486088529 avr. 198829 août 1989Allergan, Inc.Lens storage system
US48864884 août 198812 déc. 1989White Thomas CGlaucoma drainage the lacrimal system and method
US488801610 févr. 198819 déc. 1989Langerman David W"Spare parts" for use in ophthalmic surgical procedures
US489798124 déc. 19866 févr. 1990Alcon Laboratories, Inc.Method of packaging intraocular lenses and contact lenses
US49191302 nov. 198724 avr. 1990Nestle S.A.Tool for inserting compressible intraocular lenses into the eye and method
US493436315 déc. 198719 juin 1990Iolab CorporationLens insertion instrument
US493682511 avr. 198826 juin 1990Ungerleider Bruce AMethod for reducing intraocular pressure caused by glaucoma
US494643617 nov. 19897 août 1990Smith Stewart GPressure-relieving device and process for implanting
US4955903 *12 juil. 198911 sept. 1990Ceskoslovenska Akademie VedSoft intracameral lens
US496829620 déc. 19896 nov. 1990Robert RitchTransscleral drainage implant device for the treatment of glaucoma
US497173213 sept. 198820 nov. 1990Ceskoslovenska Academie VedMethod of molding an intraocular lens
US497671921 nov. 198811 déc. 1990Siepser Steven BDevice used to change corneal curvature
US50190846 août 198628 mai 1991Minnesota Mining And Manufacturing CompanyCorneal holder
US5019098 *7 mai 199028 mai 1991Essilor International Cie Generale D'optiqueSight-correcting optical component such as an intra-ocular implant or contact lens
US504108118 mai 199020 août 1991Odrich Ronald BOcular implant for controlling glaucoma
US506394214 déc. 198912 nov. 1991Corneal Contouring, Inc.Method for surgically re-profiling the cornea
US50712764 janv. 199110 déc. 1991Abbott LaboratoriesContact lens cleaning system
US507316329 janv. 199017 déc. 1991Lippman Myron EApparatus for treating glaucoma
US509283727 août 19903 mars 1992Robert RitchMethod for the treatment of glaucoma
US509844416 mars 199024 mars 1992Feaster Fred TEpiphakic intraocular lens and process of implantation
US51084282 mars 198828 avr. 1992Minnesota Mining And Manufacturing CompanyCorneal implants and manufacture and use thereof
US511235015 févr. 199112 mai 1992Cbs Lens, A California General PartnershipMethod for locating on a cornea an artificial lens fabricated from a collagen-hydrogel for promoting epithelial cell growth and regeneration of the stroma
US51239057 juin 199123 juin 1992Kelman Charles DIntraocular lens injector
US5123921 *27 mars 199123 juin 1992Nestle S.A.Synthetic intracorneal lines and method of manufacture
US513951821 mars 199018 août 1992White Thomas CMethods employed in replacement of the corneal endothelium
US517121314 août 199115 déc. 1992Price Jr Francis WTechnique for fistulization of the eye and an eye filtration prosthesis useful therefor
US51737232 oct. 199022 déc. 1992Volk Donald AAspheric ophthalmic accommodating lens design for intraocular lens and contact lens
US517860431 mai 199012 janv. 1993Iovision, Inc.Glaucoma implant
US51803623 avr. 199019 janv. 1993Worst J G FGonio seton
US518105310 mai 199019 janv. 1993Contact Lens Corporation Of AmericaMulti-focal contact lens
US51881255 oct. 199023 févr. 1993Keravision, Inc.Method for corneal curvature adjustment
US51905524 févr. 19922 mars 1993Kelman Charles DSlotted tube injector for an intraocular lens
US51923178 avr. 19929 mars 1993Irvin KalbMulti focal intra-ocular lens
US519602616 sept. 199123 mars 1993Chiron Ophthalmics, Inc.Method of implanting corneal inlay lenses smaller than the optic zone
US521166028 août 199018 mai 1993University Of South FloridaMethod for performing epikeratophakia by electrofusion
US522585818 juin 19916 juil. 1993Valdemar PortneyMultifocal ophthalmic lens
US52297978 août 199020 juil. 1993Minnesota Mining And Manufacturing CompanyMultifocal diffractive ophthalmic lenses
US524479917 déc. 199114 sept. 1993Anderson David MPreparation of a polymeric hydrogel containing micropores and macropores for use as a cell culture substrate
US525804216 déc. 19912 nov. 1993Henry Ford Health SystemIntravascular hydrogel implant
US527074426 août 199214 déc. 1993Valdemar PortneyMultifocal ophthalmic lens
US527375021 nov. 199028 déc. 1993Institute National De La Sante Et De La Recherche Medicale- InsermUncrosslinked hydrogel, process for its preparation and its uses as an article for medical and/or surgical purposes such as tubes, films, joints, implants and the like, particularly in ophthalmology
US530002030 sept. 19925 avr. 1994Medflex CorporationSurgically implantable device for glaucoma relief
US530011614 août 19925 avr. 1994Lions Eye Institute Of Western AustraliaKeratoprosthesis
US531804418 sept. 19917 juin 1994Corneal Contouring, Inc.Method and apparatus for re-profiling the cornea to correct for hyperopia
US531804710 mai 19937 juin 1994Keravision Inc.Method for corneal curvature variation
US533626110 févr. 19939 août 1994Chiron Intraoptics, Inc.Corneal inlay lenses
US53382913 févr. 199316 août 1994Pudenz-Schulte Medical Research CorporationGlaucoma shunt and method for draining aqueous humor
US534646414 avr. 199313 sept. 1994Camras Carl BMethod and apparatus for reducing intraocular pressure
US537060728 oct. 19926 déc. 1994Annuit Coeptis, Inc.Glaucoma implant device and method for implanting same
US537257718 févr. 199313 déc. 1994Ungerleider; Bruce A.Apparatus for reducing intraocular pressure
US53855829 août 199331 janv. 1995Ommaya; Ayub K.Spinal fluid driven artificial organ
US53912015 juil. 199421 févr. 1995Chiron Intraoptics, Inc.Method of using a corneal ring inlay
US539730021 avr. 199414 mars 1995Iovision, Inc.Glaucoma implant
US54053846 déc. 199311 avr. 1995Keravision, Inc.Astigmatic correcting intrastromal corneal ring
US542841217 août 199327 juin 1995Stoyan; NickMethod for treating myopia with an aspheric corneal contact lens
US543370121 déc. 199418 juil. 1995Rubinstein; Mark H.Apparatus for reducing ocular pressure
US545479610 mars 19933 oct. 1995Hood LaboratoriesDevice and method for controlling intraocular fluid pressure
US545881920 déc. 199317 oct. 1995Lions Eye Institute Of Western Australia, IncorporatedMethod of producing a keratoprosthesis
US54671491 juin 199414 nov. 1995Bausch & Lomb IncorporatedHighly visible markings for contact lenses
US54745629 mars 199412 déc. 1995Chiron Vision CorporationApparatus and method for preparing an intraocular lens for insertion
US54764451 août 199419 déc. 1995Iovision, Inc.Glaucoma implant with a temporary flow restricting seal
US549335025 août 199320 févr. 1996Seidner; LeonardMultipocal contact lens and method for preparing
US55025189 sept. 199326 mars 1996Scient Optics IncAsymmetric aspheric contact lens
US551222014 mai 199330 avr. 1996Johnson & Johnson Vision Products, Inc.Method of making a clear axis, segmented multifocal ophthalmic lens
US552063122 juil. 199428 mai 1996Wound Healing Of OklahomaMethod and apparatus for lowering the intraocular pressure of an eye
US552165616 sept. 199328 mai 1996Portney; ValdemarMethod of making an ophthalmic lens
US553049127 janv. 199425 juin 1996Essilor International Cie Generale D'optiqueSimultaneous vision ophthalmic lens for correcting presbyopia and pair of ophthalmic lenses of this kind for the same wearer
US55701429 sept. 199429 oct. 1996Scientific Optics, Inc.Asymmetric aspheric contact lens
US559118528 nov. 19947 janv. 1997Corneal Contouring Development L.L.C.Method and apparatus for reprofiling or smoothing the anterior or stromal cornea by scraping
US559823423 mars 199428 janv. 1997Innotech, Inc.Method of manufacturing toric single vision, spherical or aspheric bifocal, multifocal or progressive contact lenses
US561614825 oct. 19951 avr. 1997Staar Surgical Company, Inc.Transverse hinged deformable intraocular lens injecting apparatus
US562045025 oct. 199515 avr. 1997Staar Surgical Company, Inc.Transverse hinged deformable intraocular lens injecting apparatus
US56287948 mars 199613 mai 1997Lindstrom; Richard L.Multifocal corneal implant lens having a hydrogelo coating
US563081023 févr. 199620 mai 1997Machat; Jeffery J.Method of ophthalmological surgery
US56349431 sept. 19943 juin 1997University Of MiamiInjectable polyethylene oxide gel implant and method for production
US564327610 oct. 19951 juil. 1997AllerganApparatus and method for providing desired rotational orientation to an intraocular lens
US565710826 janv. 199612 août 1997Portney; ValdemarMultifocal ophthalmic lens
US56845604 mai 19954 nov. 1997Johnson & Johnson Vision Products, Inc.Concentric ring single vision lens designs
US57150314 mai 19953 févr. 1998Johnson & Johnson Vision Products, Inc.Concentric aspheric multifocal lens designs
US57166337 juin 199510 févr. 1998Cbs Lens, A California General PartnershipCollagen-hydrogel for promoting epithelial cell growth and regeneration of the stroma and artificial lens using the same
US572294814 févr. 19963 mars 1998Gross; Fredric J.Covering for an ocular device
US57229713 nov. 19953 mars 1998Peyman; Gholam A.Intrastromal corneal modification
US575292814 juil. 199719 mai 1998Rdo Medical, Inc.Glaucoma pressure regulator
US57661812 août 199616 juin 1998Staar Surgical Company, Inc.Spring biased deformable intraocular injecting apparatus
US577266714 nov. 199630 juin 1998Pharmacia Iovision, Inc.Method of using an intraocular lens injector
US578567420 déc. 199628 juil. 1998Mateen; Ahmed AbdulDevice and method for treating glaucoma
US580044216 oct. 19971 sept. 1998Staar Surgical Company, Inc.Deformable intraocular lens injecting system
US58005297 juin 19951 sept. 1998Baxter International, Inc.Close vascularization implant material
US580526012 sept. 19968 sept. 1998Johnson & Johnson Vision Products, Inc.Combined multifocal toric lens designs
US581083329 juil. 199622 sept. 1998AllerganDeformable lens insertion apparatus
US58171154 déc. 19956 oct. 1998Chiron Vision CorporationApparatus for resecting corneal tissue
US582408620 sept. 199620 oct. 1998Keravision, Inc.Segmented pre-formed intrastromal corneal insert
US584780214 juil. 19978 déc. 1998Johnson & Johnson Vision Products, Inc.Concentric annular ring lens designs for astigmatic presbyopes
US58556041 avr. 19975 janv. 1999Microoptix, LlcMethod and apparatus for adjusting corneal curvature using a solid filled corneal ring
US58609842 août 199619 janv. 1999Staar Surgical Company, Inc.Spring biased deformable intraocular injecting apparatus
US587261313 juin 199616 févr. 1999Innotech, Inc.Method of manufacturing contact lenses
US587643915 mai 19972 mars 1999Micooptix, LlcMethod and appartus for adjusting corneal curvature using a fluid-filled corneal ring
US58882436 juin 199530 mars 1999Keravision, Inc.Hybrid intrastromal corneal ring
US59138982 déc. 199622 juin 1999Staar Surgical Company, Inc.Intraocular contact lens and method of implantation
US591918525 avr. 19976 juil. 1999Peyman; Gholam A.Universal implant blank for modifying corneal curvature and methods of modifying corneal curvature therewith
US59282452 août 199627 juil. 1999Staar Surgical Company, Inc.Deformable intraocular lens injecting apparatus with transverse hinged lens cartridge
US59299687 avr. 199727 juil. 1999Cotie; Robert L.Scleral-corneal contact lens
US59299698 oct. 199727 juil. 1999Johnson & Johnson Vision Products, Inc.Multifocal ophthalmic lens
US59415835 oct. 199824 août 1999Raimondi; KentContact lens insertion and manipulation assembly and method
US594475217 sept. 199731 août 1999Kera Vision, Inc.Astigmatic correcting intrastromal corneal insert
US594549822 mars 199631 août 1999Novartis AgPolysiloxane-comprising perfluoroalkyl ethers and the preparation and use thereof
US59647487 déc. 199512 oct. 1999Peyman; Gholam A.Intrastromal corneal modification
US596477624 sept. 199712 oct. 1999Peyman; Gholam A.Internal keratome apparatus and method for using the same to form a pocket/flap between layers of a live cornea
US597615025 août 19982 nov. 1999Alcon Laboratories, Inc.Intraocular lens injection system
US600751025 oct. 199628 déc. 1999Anamed, Inc.Implantable devices and methods for controlling the flow of fluids within the body
US60105102 juin 19984 janv. 2000Alcon Laboratories, Inc.Plunger
US602444831 mars 199815 févr. 2000Johnson & Johnson Vision Products, Inc.Contact lenses bearing identifying marks
US60333953 nov. 19977 mars 2000Peyman; Gholam A.System and method for modifying a live cornea via laser ablation and mechanical erosion
US605099918 déc. 199718 avr. 2000Keravision, Inc.Corneal implant introducer and method of use
US605599021 avr. 19982 mai 2000Thompson; Keith P.Polymerizing gel intrakeratophakia-PGI
US606617020 mars 199823 mai 2000Microoptix LlcMethod and apparatus for adjusting corneal curvature
US60798262 avr. 199827 juin 2000Bausch & Lomb IncorporatedMethod for identifying characteristics of contact lenses
US608323119 avr. 19994 juil. 2000Alcon Laboratories, Inc.Asymmetric intraocular lens injection cartridge
US60862027 avr. 199911 juil. 2000Essilor International (Compagnie Generale D'optique)Method of producing angular tolerance markings for lenses for correcting astigmatism, and associated lenses
US609014113 août 199718 juil. 2000Lindstrom; Richard L.Small intracorneal lens
US6102946 *23 déc. 199815 août 2000Anamed, Inc.Corneal implant and method of manufacture
US61101662 oct. 199629 août 2000Escalon Medical CorporationMethod for corneal laser surgery
US61201485 oct. 199819 sept. 2000Bifocon Optics GmbhDiffractive lens
US612973315 avr. 199910 oct. 2000Allergan Sales, Inc.Apparatus for holding intraocular lenses and injectors, and methods for using same
US614296927 juil. 19987 nov. 2000Anamed, Inc.Sutureless implantable device and method for treatment of glaucoma
US61430011 oct. 19997 nov. 2000Alcon Laboratories, Inc.Asymmetric intraocular lens injection cartridge
US615924129 mars 199912 déc. 2000Joseph Y. LeeMethod and apparatus for adjusting corneal curvature using multiple removable corneal implants
US61835135 juin 19986 févr. 2001Bausch & Lomb Surgical, Inc.Intraocular lens packaging system, method of producing, and method of using
US61970192 mars 19996 mars 2001Gholam A. PeymanUniversal implant blank for modifying corneal curvature and methods of modifying corneal curvature therewith
US619705727 oct. 19986 mars 2001Gholam A. PeymanLens conversion system for teledioptic or difractive configurations
US6197058 *22 mars 19996 mars 2001Valdemar PortneyCorrective intraocular lens system and intraocular lenses and lens handling device therefor
US620353829 sept. 199720 mars 2001Gholam A. PeymanIntrastromal corneal modification
US620354929 déc. 199820 mars 2001Duckworth & Kent LimitedInjectors for intraocular lenses
US620691913 janv. 199927 mars 2001Joseph Y. LeeMethod and apparatus to correct refractive errors using adjustable corneal arcuate segments
US62100054 févr. 19993 avr. 2001Valdemar PortneyMultifocal ophthalmic lens with reduced halo size
US621401517 sept. 199810 avr. 2001Bausch & Lomb Surgical, Inc.Apparatus and method for preparing an intraocular lens for insertion
US62140446 juin 199510 avr. 2001Keravision, Inc.Hybrid intrastromal corneal ring
US621757116 sept. 199917 avr. 2001Gholam A. PeymanIntrastromal corneal modification
US622106720 oct. 199524 avr. 2001Gholam A. PeymanCorneal modification via implantation
US622811417 nov. 19978 mai 2001Joseph Y. LeeAdjustable corneal ring
US62481116 août 199919 juin 2001Allergan Sales, Inc.IOL insertion apparatus and methods for using same
US625075715 déc. 199926 juin 2001Johnson & Johnson Vision Products, Inc.Hybrid refractive birefringent multifocal ophthalmic lenses
US625111429 oct. 199926 juin 2001Allergan Sales, Inc.Rotatable IOL insertion apparatus and method for using same
US62646483 mars 199224 juil. 2001Bausch & Lomb IncorporatedCorneal curvature modification via internal ablation
US626776822 mars 199931 juil. 2001AllerganLens protector for intraocular lens inserter
US627128126 août 19997 août 2001Medennium, Inc.Homopolymers containing stable elasticity inducing crosslinkers and ocular implants made therefrom
US628044917 avr. 199828 août 2001Tekia, Inc.Ophthalmologic insertor apparatus and methods of use
US62804702 mars 199928 août 2001Gholam A. PeymanIntrastromal corneal modification
US628359524 févr. 20004 sept. 2001Joseph L. BregerPinhole presbyopic contact lenses
US6325509 *20 août 19994 déc. 2001Art Optical Contact Lens, Inc.Low-mass ophthalmic lens
US6361560 *27 août 199926 mars 2002Anamed, Inc.Corneal implant and method of manufacture
US637196019 mai 199816 avr. 2002Bausch & Lomb Surgical, Inc.Device for inserting a flexible intraocular lens
US639123018 févr. 200021 mai 2002Bausch & Lomb IncorporatedIntraocular lens manufacturing process
US639827715 mars 20014 juin 2002Mcdonald Marguerite B.Contact lens insertion device
US639878919 oct. 20004 juin 2002Alcon Universal, Ltd.Intraocular lens injector cartridge
US642857211 janv. 19996 août 2002Menicon Co., Ltd.Intraocular ring
US643568111 janv. 200120 août 2002Valdemar PortneyMultifocal ophthalmic lens with reduced halo size
US643609221 mars 200020 août 2002Gholam A. PeymanAdjustable universal implant blank for modifying corneal curvature and methods of modifying corneal curvature therewith
US644751922 mars 200010 sept. 2002Allergan Sales, Inc.Apparatus for holding intraocular lenses and injectors, and methods for using same
US644752019 mars 200110 sept. 2002Advanced Medical Optics, Inc.IOL insertion apparatus with IOL engagement structure and method for using same
US645814110 mars 20001 oct. 2002Gholam A. PeymanMethod and apparatus for creating a flap in the cornea and incisions or shrinkage under the flap to correct vision disorders
US647170821 déc. 200029 oct. 2002Bausch & Lomb IncorporatedIntraocular lens and additive packaging system
US64748148 sept. 20005 nov. 2002Florida Optical Engineering, IncMultifocal ophthalmic lens with induced aperture
US651117819 juil. 199928 janv. 2003Johnson & Johnson Vision Care, Inc.Multifocal ophthalmic lenses and processes for their production
US652738922 mars 20024 mars 2003Advanced Medical Optics, Inc.Multifocal ophthalmic lens
US653728317 août 200125 mars 2003Alcon, Inc.Intraocular lens shipping case and injection cartridge
US654361012 sept. 20008 avr. 2003Alok NigamSystem for packaging and handling an implant and method of use
US654428618 juil. 20008 avr. 2003Tissue Engineering Refraction, Inc.Pre-fabricated corneal tissue lens method of corneal overlay to correct vision
US655130727 avr. 200122 avr. 2003Gholam A. PeymanVision correction using intrastromal pocket and flap
US655442517 oct. 200029 avr. 2003Johnson & Johnson Vision Care, Inc.Ophthalmic lenses for high order aberration correction and processes for production of the lenses
US655799814 juin 20026 mai 2003Advanced Medical Optics, Inc.Multifocal ophthalmic lens with reduced halo size
US658199326 avr. 200124 juin 2003Alok NigamSystem for packaging and handling an implant and method of use
US658207630 août 200024 juin 2003Johnson & Johnson Vision Care, Inc.Ophthalmic lenses useful in correcting astigmatism and presbyopia
US65892031 août 20008 juil. 2003Peter MitrevGlaucoma drainage device implant
US658928011 mai 20018 juil. 2003Jeffrey E. KoziolMethod for producing a multifocal corneal surface using intracorneal microscopic lenses
US659259119 déc. 200015 juil. 2003Micro Medical Devices, Inc.Foldable lens delivery system
US66050935 janv. 200012 août 2003Tekia, Inc.Device and method for use with an ophthalmologic insertor apparatus
US66075371 févr. 200019 août 2003Helmut BinderInjector for implanting a folded intraocular lens, container for storing and transporting the injector and method for ejecting the lens in a folded state
US66075566 sept. 200019 août 2003Anamed, Inc.Corneal implant and method of manufacture
US6623522 *7 nov. 200123 sept. 2003Alok NigamMyopic corneal ring with central accommodating portion
US662694119 oct. 200130 sept. 2003Anamed, Inc.Corneal implant and method of manufacture
US66299792 mai 20007 oct. 2003Staar Surgical Company, Inc.Implantation device with deformable nozzle tip for implanting a deformable intraocular lens
US66322446 sept. 200014 oct. 2003Anamed, Inc.Corneal implant and method of manufacture
US664887730 juin 200018 nov. 2003Intralase Corp.Method for custom corneal corrections
US665702910 oct. 20012 déc. 2003Bausch & Lomb IncorporatedHigh refractive index hydrogel compositions for ophthalmic implants
US666688722 oct. 200123 déc. 2003Thinoptx, Inc.Deformable intraocular multi-focus lens
US667311219 oct. 20016 janv. 2004Anamed, Inc.Corneal implant and method of manufacture
US670910331 oct. 200223 mars 2004Johnson & Johnson Vision Care, Inc.Methods for designing multifocal ophthalmic lenses
US671284826 juil. 199930 mars 2004Staar Surgical Company, Inc.Deformable intraocular lens injecting apparatus with transverse hinged lens cartridge
US672310413 mars 200220 avr. 2004Advanced Medical Optics, Inc.IOL insertion apparatus and method for using same
US673350712 avr. 200211 mai 2004Advanced Medical Optics, Inc.Intraocular lens insertion apparatus
US673352625 avr. 200211 mai 2004Advanced Medical Optics, Inc.Method of improving adherence and centering of intra-corneal implants on corneal bed
US6808262 *14 juin 200126 oct. 2004Novartis AgMultifocal contact lens with aspheric surface
US68241788 nov. 200230 nov. 2004Alok NigamSystem for packaging and handling an implant and method of use
US687523215 janv. 20025 avr. 2005Anamed, Inc.Corneal implant and method of manufacture
US6879402 *15 nov. 200212 avr. 2005Zygo CorporationScanning interferometer for aspheric surfaces and wavefronts
US68811971 nov. 200019 avr. 2005Anamed, Inc.Sutureless implantable device and method for treatment of glaucoma
US689346117 juin 200317 mai 2005Anamed, Inc.System for packaging and handling an implant and method of use
US71283519 févr. 200531 oct. 2006Anamed, Inc.System for packaging and handling an implant and method of use
US20010051826 *6 févr. 200113 déc. 2001Bogaert Theo T. M.Intraocular lenses
US20020101563 *24 janv. 20021 août 2002Menicon Co., Ltd.Contact lens
US2003001404213 juil. 200116 janv. 2003Tibor JuhaszMethod of creating stromal pockets for corneal implants
US200300784879 août 200224 avr. 2003Jeffries Robert E.Ocular pressure measuring device
US20030088313 *7 nov. 20018 mai 2003Alok NigamMyopic corneal ring with central accommodating portion
US2004004926730 juin 200311 mars 2004Alok NigamMyopic corneal ring with central accommodating portion
US2005008048529 nov. 200414 avr. 2005Alok NigamCorneal implant and method of manufacture
US2005011384429 nov. 200426 mai 2005Alok NigamSystem for packaging and handling an implant and method of use
US2005011973811 janv. 20052 juin 2005Alok NigamMyopic corneal ring with central accommodating portion
US2005014371724 févr. 200430 juin 2005Peyman Gholam A.Method of treatment of refractive errors using subepithelial or intrastromal corneal inlay with bonding coating
US2005017839423 août 200418 août 2005Intralens Vision, Inc.Method for keratophakia surgery
US2005018235018 avr. 200518 août 2005Alok NigamSutureless implantable device and method for treatment of glaucoma
US2005024601615 avr. 20053 nov. 2005Intralens Vision, Inc.Implantable lenses with modified edge regions
US20060116762 *30 nov. 20041 juin 2006Xin HongAspheric lenticule for keratophakia
US200602120417 juin 200621 sept. 2006Alok NigamSystem for Packaging and Handling an Implant and Method of Use
US2006023543015 avr. 200519 oct. 2006Intralens Vision, Inc.Corneal implant injector assembly and methods of use
US200701297971 déc. 20057 juin 2007Revision Optics, Inc.Intracorneal inlays
US2007020357730 oct. 200630 août 2007Revision Optics, Inc.Small Diameter Inlays
US200702554011 mai 20061 nov. 2007Revision Optics, Inc.Design of Inlays With Intrinsic Diopter Power
US200702809941 juin 20066 déc. 2007Cunanan Crystal MOcular Tissue Separation Areas With Barrier Regions For Inlays Or Other Refractive Procedures
USRE3707131 janv. 200027 févr. 2001Canadian Contact Lens Laboratories Ltd.Marked contact lens bearing optical marking element
DE3208729A111 mars 198222 sept. 1983Joerg Dr Med KrumeichPlastic lens
EP0308077A219 août 198822 mars 1989Nestle S.A.Synthetic intracorneal lens
EP0420549A224 sept. 19903 avr. 1991HYMEDIX International, Inc.Corneal lens implant
WO1996026690A14 mars 19966 sept. 1996Keravision, Inc.Corneal implant for changing refractive properties
WO1998008549A114 août 19975 mars 1998The Lions Eye Institute Of Western Australia IncorporatedOcular socket prosthesis
WO1998048715A111 mars 19985 nov. 1998Peyman Gholam AA universal implant blank for modifying corneal curvature and methods of modifying corneal curvature therewith
WO1999017691A121 mai 199815 avr. 1999Ras Holding CorporationScleral prosthesis for treatment of presbyopia and other eye disorders
WO1999021513A117 avr. 19986 mai 1999Tekia, Inc.Ophthalmologic insertor apparatus and methods of use
WO1999030645A218 déc. 199824 juin 1999Keravision, Inc.Corneal implant methods and pliable implant therefore
WO2000038594A122 déc. 19996 juil. 2000Anamed, Inc.Corneal implant and method of manufacture
WO2003041616A18 nov. 200222 mai 2003Peyman Gholam AMethod and apparatus for alignment of intracorneal inlay
WO2003061518A217 janv. 200331 juil. 2003Edward PerezMethods for producing epithelial flaps on the cornea and for placement of ocular devices and lenses beneath an epithelial flap or membrane, epithelial delaminating devices, and structures of epithelium and ocular devices and lenses
WO2003101341A23 juin 200311 déc. 2003Scientific Optics, Inc.Method and system for improving vision
Citations hors brevets
Référence
1Cheng, et al.; "Predicting subjective judgment of best focus with objective image quality metrics"; Journal of Vision; vol. 4, pp. 310-321, 2004.
2Churms, P.W., "The Theory and Computation of Optical Modifications to the Cornea in Refractive Keratoplasty," American Journal of Optometry & Physiological Optics, 56:2, pp. 67-74, Feb. 1979.
3Dishler, Jon et al.; U.S. Appl. No. 11/692,835 entitled "Insertion system for corneal implants," filed Mar. 28, 2007.
4Lang, Alan et al.; U.S. Appl. No. 11/738,349 entitled "Biomechanical design of intracorneal inlays," filed Apr. 20, 2007.
5Liou, H. L. et al., "Anatomically accurate, finite model eye for optical modeling", Journal of the Optical Society of America, vol. 14, No. 8, Aug. 1997.
6Marsack,et al.; "Metrics of optical quality derived from wave aberrations predict visual performance"; Journal of Vision; vol. 4; pp. 322-328; 2004.
7Warsky, M.A. et al., "Predicting Refractive Alterations with Hydrogel Keratophakia," Investigative Opthalmology & Visual Science, vol. 26, pp. 240-243, Feb. 1985.
Référencé par
Brevet citant Date de dépôt Date de publication Déposant Titre
US846994823 août 201025 juin 2013Revision Optics, Inc.Methods and devices for forming corneal channels
US85407272 mars 201224 sept. 2013Revision Optics, Inc.Insertion system for corneal implants
US866873522 oct. 201211 mars 2014Revision Optics, Inc.Corneal implant storage and delivery devices
US900528010 avr. 201214 avr. 2015Revision Optics, Inc.System for packaging and handling an implant and method of use
US91950745 avr. 201324 nov. 2015Brien Holden Vision InstituteLenses, devices and methods for ocular refractive error
US92012504 oct. 20131 déc. 2015Brien Holden Vision InstituteLenses, devices, methods and systems for refractive error
US927182813 juil. 20121 mars 2016Revision Optics, Inc.Corneal implant retaining devices and methods of use
US934556922 oct. 201224 mai 2016Revision Optics, Inc.Corneal implant storage and delivery devices
US95352635 avr. 20133 janv. 2017Brien Holden Vision InstituteLenses, devices, methods and systems for refractive error
US953914312 mars 201510 janv. 2017Revision Optics, Inc.Methods of correcting vision
US95417734 oct. 201310 janv. 2017Brien Holden Vision InstituteLenses, devices, methods and systems for refractive error
US954984814 sept. 201224 janv. 2017Revision Optics, Inc.Corneal implant inserters and methods of use
US95753349 déc. 201421 févr. 2017Brien Holden Vision InstituteLenses, devices and methods of ocular refractive error
US975993015 oct. 201512 sept. 2017Brien Holden Vision InstituteLenses, devices, systems and methods for refractive error
DE102011106289A11 juil. 20113 janv. 2013Carl Zeiss Meditec AgHornhautimplantat
WO2013004590A128 juin 201210 janv. 2013Carl Zeiss Meditec AgCorneal implant
Classifications
Classification aux États-Unis623/5.11, 623/6.23
Classification internationaleA61F2/14
Classification coopérativeA61F2/147, A61F2/164, A61F2/142, A61F2/14
Classification européenneA61F2/14
Événements juridiques
DateCodeÉvénementDescription
21 juin 2004ASAssignment
Owner name: ANAMED, INC., CALIFORNIA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:MILLER, TROY;REEL/FRAME:015480/0477
Effective date: 20040615
5 avr. 2007ASAssignment
Owner name: REVISION OPTICS, INC., CALIFORNIA
Free format text: CHANGE OF NAME;ASSIGNOR:INTRALENS VISION, INC.;REEL/FRAME:019122/0362
Effective date: 20050818
Owner name: INTRALENS VISION, INC., CALIFORNIA
Free format text: CHANGE OF NAME;ASSIGNOR:ANAMED, INC.;REEL/FRAME:019122/0270
Effective date: 20050303
22 janv. 2014FPAYFee payment
Year of fee payment: 4